Diagnostic ultrasound transducer

ABSTRACT

An ultrasound transducer includes an array of PZT elements mounted on a non-recessed distal surface of a backing block. Between each element and the backing block is a conductive region formed as a portion of a metallic layer sputtered onto the distal surface. Traces on a longitudinally extending circuit board—preferably, a substantially rigid printed circuit board, which may be embedded within the block—connect the conductive region, and thus the PZT element, with any conventional external ultrasound imaging system. A substantially “T” or “inverted-L” shaped electrode is thereby formed for each element, with no need for soldering. At least one longitudinally extending metallic member mounted on a respective lateral surface of the backing block forms a heat sink and a common electrical ground. A thermally and electrically conductive layer, such as of foil, transfers heat from at least one matching layer mounted on the elements to the metallic member.

FIELD OF THE INVENTION

This invention relates to an ultrasonic transducer for use in diagnosticimaging.

BACKGROUND OF THE INVENTION Description of the Related Art

The importance of diagnostic ultrasound imaging is widely recognized,and has grown as imaging resolution and the range of available uses andfeatures have steadily increased. Once an expensive luxury availableonly in the best-equipped hospitals, diagnostic ultrasound imaging isnow a commonly and almost routinely offered procedure even in someindividual physician's offices. Perhaps more importantly, someultrasound imaging systems are now portable and inexpensive enough tohave even in small offices, or in places such as in developing countrieswith relatively small budgets for such diagnostic tools.

The quality of an ultrasound image is directly affected by many factorsand in particular by the properties of the transducer used to generatethe necessary pattern of ultrasonic signals and to receive their echoreturns. Accordingly, work is constantly in progress to improve almostevery major component of a transducer, the materials used in it, and themethods of manufacturing it. During the past 30 years or so, just a fewof the large number of improvements include better active materials,triple matching layers, better kerf filling, low-attenuation lensmaterials, heat treatments and heat sinks, and flex circuitinterconnects.

Typically, piezoelectric elements within a transducer are formed as anarray and are selectively activated electrically to produce a desiredscan pattern. The same array is then switched to receive the returnsignals, which are then converted back into electrical signals that areprocessed using known methods. Individual and separate control ofelements presumes, however, separate electrical leads in the form ofwires, or traces on a circuit board, either printed (PCB) or flexible(flex circuit).

This reality leads to several challenges and trade-offs relating to suchissues as, among many others, cross-talk, impedance, physicalrobustness, heat, integrity and ease of bonding, manufacturing cost andcomplexity, and even comfort in use. For example, strong lead wires mayprovide physical robustness, but they may also cause the transducercable to be so bulky and stiff that it is cumbersome for an operator tomaneuver over the body of a patient. However, fine wires or traces thatallow for a light, flexible cable are more prone to breaking. As anotherexample, certain transducer structures may be specially designed to bemanufactured with certain materials, such as in a backing layer, but maythen be difficult to adapt to new materials without difficult and costlychanges in the structure and manufacturing procedures.

Many different transducer structures and cabling (including single,double, and multi-layer flex circuits) and interconnect arrangementshave, accordingly, been proposed in different contexts involvingdiagnostic ultrasound imaging. The following U.S. patents, for example,represent proposed solutions to some of the many problems involved indifferent contexts of diagnostic ultrasound imaging transducers:

U.S. Pat. No. 5,559,388 (Lorraine, et al., “High density interconnectfor an ultrasonic phased array and method for making”);

U.S. Pat. No. 5,722,137 (Lorraine, et al., “Method for making a highdensity interconnect for an ultrasonic phased array”);

U.S. Pat. No. 5,567,657 (Wojnarowski, et al., “Fabrication andstructures of two-sided molded circuit modules with flexibleinterconnect layers”);

U.S. Pat. No. 5,617,865 (Palczewska, et al., “Multi-dimensionalultrasonic array interconnect”)

U.S. Pat. No. 5,920,972 (Palczewska, et al., “Interconnection method fora multilayer transducer array”);

U.S. Pat. No. 6,994,674 (Sheljaskow, et al., “Multi-dimensionaltransducer arrays and method of manufacture”);

U.S. Pat. No. 5,703,400 (Wojnarowski, et al., “Fabrication andstructures of two-sided molded circuit modules with flexibleinterconnect layers”);

U.S. Pat. No. 5,923,115 (Mohr, III, et al., “Low mass in the acousticpath flexible circuit interconnect and method of manufacture thereof”);

U.S. Pat. No. 6,541,896 (Piel, Jr., et al., “Method for manufacturingcombined acoustic backing and interconnect module for ultrasonicarray”);

U.S. Pat. No. 6,580,034 (Daane, et al., “Flexible interconnect cablewith ribbonized ends”);

U.S. Pat. No. 6,651,318 (Buck, et al., “Method of manufacturing flexibleinterconnect cable”);

U.S. Pat. No. 6,734,362 (Buck, et al., “Flexible high-impedanceinterconnect cable having unshielded wires”); and

U.S. Pat. No. 7,229,292 (Haider, et al., “Interconnect structure fortransducer assembly”).

There is nonetheless always room for improvement, not only in general,but also in the specific context of providing a transducer that issuitable for use beyond the well-controlled world of a diagnostic unitin a large-budget hospital. For example, a transducer for use in thefield, or for wide-scale use in developing countries, should ideally berelatively easy to build and the component costs should be relativelylow (to allow for greater numbers for a given budget); the performanceshould be as little limited or reduced as possible; it should be easy toadapt the transducer and its manufacturing process to take advantage ofany newly developed materials, or to design changes such as in thenumber of matching layers. The transducer should also be physicallyrobust and should preferably be more thermally tolerant thanconventional probes. This invention at least partially meets one or moreof these needs.

SUMMARY OF THE INVENTION

The invention relates to a diagnostic ultrasound transducer that has anarray of electro-acoustic elements, such as PZT elements, mounted on abacking block. At least one matching layer is mounted on the array, aswell as (for most implementations) a lens.

According to one aspect of some embodiments of the invention, thesurface of the backing block on which the array is mounted is planar andnon-recessed. For each electro-acoustic element in the array, an area ofelectrically conductive material is formed, for example by sputtering,on a corresponding portion of a contact surface of the backing block andin electrical contact with the electro-acoustic element.

In certain embodiments, a substantially rigid printed circuit board(PCB) is secured to or even within the backing block and extends in alongitudinal direction substantially perpendicular to the contactsurface. For each electro-acoustic element, at least one electricallyconductive trace is made on the circuit board in electrical contact withthe corresponding contact surface portion and thereby with theelectro-acoustic element. This creates a solder-free electrical signalpath through the trace to the electro-acoustic element.

The circuit board may be either embedded within the backing block, whichmakes for easy mounting and secure positioning in a backing blocker usedto mold the backing block, or mounted on a lateral surface of thebacking block. Together with the traces and the conductive layersputtered (for example) on the contact surface of the backing block,these embodiments provide a substantially “T” or “inverted-L”-shapedelectrode for each element, with no need for soldering to provide goodelectrical contact.

At least one metallic member is preferably located on at least one sidesurface of the backing block, and extends longitudinally at least as faras the array. This member may be made as physically separate (butpreferably electrically connected) plate- or sheet-like structures oneither elevational side of the transducer, or as “arms” of a singleframe- or box-like member that contacts the backing block on threesides. The metallic member may form a common electrical ground contactfor the transducer. Where needed to prevent electrical shorting of thearray elements' electrodes, an electrically insulating element may bemounted on the backing block to separate the metallic member from theelectrically conductive material on the contact surface of the backingblock.

At least one acoustic matching layer will normally be mounted on atransmitting surface of the array. An edge region of each metallicportion of each metallic member is preferably in direct or indirectthermal contact with a respective edge portion of at least one of thematching layers. For direct thermal contact, the metallic member extendslongitudinally far enough to physically contact either side(elevational) or bottom edges of at least the innermost (closest to thebacking block) matching layer. Indirect thermal contact may be providedusing a thermally conductive, metallic layer, such as foil, locatedeither between matching layers, or between at least the innermostacoustic matching layer and the array. The metallic member mounted onthe sides of the backing block thereby may form not only a commonelectrical ground, but also a heat sink for heat flowing through thethermally conductive, metallic layer, as well as laterally from theelectro-acoustic elements.

The invention also encompasses a method for making the transducer, whichis especially advantageous for implementing embodiments of the inventionin which the circuit board is a rigid PCB. The method includes: applyingelectrically conductive traces to at least one surface of the PCB;forming the backing block with the PCB secured to it; sputtering anelectrically conductive layer onto the distal, non-recessed, planarcontact surface of the backing block and a top edge of the PCB; mountingan electro-acoustic material on the contact surface of the backingblock; mounting at least one matching layer on the electro-acousticmaterial; dicing the matching layer, the electro-acoustic material, andthe electrically conductive layer into an array of electricallyseparated portions, each portion of the electro-acoustic materialthereby forming a separate electro-acoustic element and each portion ofthe electrically conductive layer thereby forming an electrodeconnecting the electro-acoustic element to at least one of the traces;and, on at least one side of the backing block, mounting the metallicmember (either the single “box-like” structure or electrically connectedby physically separate elements such as plates) in contact with alateral edge of the backing block and electrically insulated from theelectrically conductive layer portion.

If “T” electrodes are to be made, then the PCB may be embedded in thebacking block during the forming of the backing block. The rigidity ofthe PCB (as compared with, for example, a flex circuit), makes it mucheasier to ensure that the PCB location is fixed in the backing blocker(the structure that acts as a frame and mold for manufacturing thebacking block), with less or no need for restraining or other supportingstructures that also get embedded in the backing block and may causeimage noise.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows a partially cut-away view from the side of the internalstructure of one embodiment of an ultrasound probe according to theinvention.

FIG. 2 is a partially cut-away view from the top of the transducer,taken along line II-II in FIG. 1.

FIG. 3 shows a feature in which heat-conducting metallic members such asplates help lead heat away from not only an array of electro-acousticelements, but also from at least one matching layer.

FIG. 4 shows a flex circuit used in place of a substantially rigidprinted circuit board.

FIG. 5 illustrates a metallic “box” that encloses much of a backingblock and other structures of the probe.

FIGS. 6A-6F illustrate various steps in a manufacturing process for oneembodiment of the transducer.

DETAILED DESCRIPTION

FIG. 1 shows a partially cut-away view from the side of the internalstructure of an ultrasound probe, that is, transducer 100 according toone embodiment of the invention. In FIGS. 1 and 2, coordinate systemsindicating the conventional reference directions are indicated. Here,AZ, EL, and LON indicate the azimuthal, elevational, and longitudinaldirections. The longitudinal direction, which is sometimes referred toas the axial direction, is the direction in which it is assumed thatultrasound energy will primarily radiate from each element of thetransducer array. Viewed as in FIG. 1 and as the transducer is used inpractice, the top of the transducer is the distal end and the bottom isthe proximal end.

In particular, FIG. 1 shows one of typically many elements in anultrasound transducer array—oriented as in FIG. 1, the array elementsextend perpendicular to the plane of the figure, that is, in anazimuthal direction. Each element of the array will, in typicalimplementations, have the same essential structure as the one shown inFIG. 1. FIG. 2 shows a simplified cross-sectional view of the probetaken along line II-II of FIG. 1.

The invention may be used for probes with any chosen number of arrayelements consistent with the intended use for ultrasound imaging. Notethat none of the figures is necessarily to scale—those skilled in thedesign of ultrasound transducers will choose the dimensions of thevarious features to meet the needs of each given implementation of theinvention.

One or more outer and/or inner (for multi-layer) surfaces of a printedcircuit board (PCB) 102 is provided in any known manner with one or moreelectrically conductive traces 104, 105 either as needed or desired fora given design choice. As is well known, traces for adjacent elementsare often made on opposite sides of whatever substrate is used to carrythem. This allows for a greater array density (element pitch) sincetraces for adjacent elements will not be too close together or too thin.Multilayer substrates allow for even greater density by providing foreven more electrically separated surfaces to make traces on. Theplacement of traces is a design choice that transducer designers arewell used to making. Note that, viewed as in FIG. 1, the PCB extendsperpendicular to the plane of the figure.

In one prototype of the invention, the PCB 102 was a thin multilayerPCB. In general, the PCB is substantially rigid. Of course, no circuitboard, PCB or otherwise, is completely rigid in the sense that it cannotbe bent. In this description, “rigid” means that under normal operatingconditions, neither the material nor the fabrication for the PCB 102 orthe traces 104, 105 is chosen with the expectation that they will needto withstand any bending stress. By way of contrast, a flex circuit bythis definition is not rigid.

The traces 104, 105 lead corresponding electrical signals from and tolead wires 106, 107, which are electrically connected with the mainprocessing and control system (not shown) of the ultrasonic imagingdevice in any known manner. In FIG. 2, the wires are shown collectivelyas 206 entering a standard ribbon cable 200, which will then leadsignals between the probe and the main unit of the ultrasound imagingsystem. Other arrangements for connecting traces electrically with leadwires are known and may be used with any of the embodiments of thisinvention.

A backing block 110, which may be made of any conventional material suchas epoxy mixed with some heavy, sound-absorbing material(s), forms thebase of the probe. In the embodiment shown in FIG. 1, the PCB 102 isembedded in the backing block 110. In other words, the backing block 110is molded around the PCB 102, for example, such that the PCB 102 extendssubstantially through the middle of the backing block 110 in thelongitudinal direction.

This arrangement is not necessary, however, but rather the PCB 102 couldinstead be mounted on a side of the backing block 110, out of theacoustic path, which may be advantageous in high-frequency applications.The precise position of the PCB 102 can be determined by the chosenposition of the blocking and mixing tool, and of the fixture of thelamination and dicing tool. The design and use of such tools andfixtures are well known in the field of transducer manufacture suchthat, after proper design and adjustment of the equipment, no specialskills will be needed to manufacture the probe.

It would also be possible to include more than one PCB (each with itsown traces) within or on the backing block 110, for example, in a 1.5—orhigher-dimensional array. The structures and techniques described heremay also be modified in ways apparent to those skilled in ultrasoundtransducer design to accommodate even non-linear array architectures.

An array 114 of electro-acoustic elements made, for example, of asuitable electro-ceramic material such as lead zirconate titanate (PZT)is mounted on the backing block 110 and is diced and filled in anyconventional manner to form several elements, of which one—element PZTelement 115—is shown in FIG. 1; it would also be possible to form thearray as a series of individual electro-acoustic crystals. PZT elementsformed by dicing a single block are, however, the most common suchelements in ultrasound transducers and are assumed in this discussionfor the sake of succinctness and clarity. Their properties, fabricationmethods, proper dimensioning and operation are well-understood and aretherefore not described in greater detail here.

Metallic members such as sheets or plates 120, 121, or a sufficientlythick deposit of some metallic material (here, “plate(s)” just for thesake of simplicity), may be bonded in any known way on either side ofthe backing block 100 and extend in contact with most and preferably allof the lateral edges (again, viewed as in FIG. 1) of the PZT elements ofthe array 115. These plates may be made of copper, aluminum, or anyother metal that conducts heat well so as to form a thermal path forheat to flow away from the PZT element 115 and the backing block 110 toany external sink. The plates 120, 121, which are preferablyelectrically connected in known manner (including being portions of asingle enclosing member—see below) also provide an effective commonground for various electrically conductive parts of the transducer andin particular for the PZT elements. If the PCB 102 is mounted on theside of the backing block 110, then the metallic plate 120, 121 on thatside will either be mounted on the external surface of the PCB (assumingeither that there are no traces on that side or that the traces are insome known way electrically isolated from the plate), or that plate maybe omitted altogether.

A layer 125 of a conductive metal such as layered gold, or gold onnickel, is applied, for example deposited by sputtering, onto the topsurface (thus, a contact surface) of the backing block backing block110. In one prototype of the invention, the conductive layer 125 was a3000 Å thick layer of sputtered gold, which is relatively easy to docompared with what is typically required for element contact in priorart probes. Preferably, the entire top surface of the backing block 110is provided with the conductive layer 125 so as to provide the bestelectrical contact with the PZT element 115. To ensure good electricalcontact, the bottom surface of the PZT element 115 may also be providedwith a similar sputtered-on conductive layer 126, although this will inmany cases be an optional feature. The upper surface of the backingblock 110 is preferably prepared by being smoothed and polished so as tohave as flat an upper surface as possible, thus providing full surfacecontact between the layer 125 and the underside of the element 115.

The traces 104, 105 extend up to and join with the conductive layer 125,thereby forming an uninterrupted electrical path to each PZT elementwith no need for soldering. In essence, a solder-free, “T-shaped”electrode (the traces 104, 105 on the PCB 102 and the layer 125) isprovided, with full electrical contact with the underside of PZTelement. Of course, if the PCB is mounted on the side of the backingblock 110 and is not embedded, then the electrode will have the shape ofan inverted “L”. Although in theory (and often in practice) only onetrace will be needed per PZT element to provide electrical contact, morethan one trace per element may be provided to increase the likelihoodand integrity of electrical contact with the conductive layer 125 andthus with the PZT element.

As FIG. 2 illustrates, dicing cuts 210, 212 (only two are labeled, forsimplicity), extend all the way through the matching layer(s), the PZTlayer and the conductive layer 125 into the backing block so as toisolate the PZT elements electrically from each other, in particular, sothat the metallic layer 125 will not electrically short any of theelements. One should keep in mind that the figures are not necessarilyto scale—in most actual probes made according to any embodiment, theremay be well over 100 (and in some cases several hundred) PZT elements ina linear array, and even more in a 2-D array. Merely for the sake ofclarity, the figures do not attempt (or, for those skilled in transducerdesign and manufacture, need) to show the sizes of the elements 115 inthe figures relative to the actual dimensions of, for example, the widthof a typical lens 144 or the length of typical traces. Moreover, FIG. 2also illustrates how traces for, for example, adjacent PZT elements maybe located on opposite sides of the PCB 102, such that only traces 104are visible in FIG. 2.

The conductive layer 125 is preferably electrically insulated from themetallic plates 120, 121, for example by strips 130, 131 of anon-conductive material such as Kapton/polyimide bonded to the sides ofthe backing block 110 and the PZT element 115 where these meet. Viewedas in FIG. 1, these strips would extend perpendicular to the plane ofthe figure, in the azimuthal direction, along the width of the array 114(on both or only one side, depending on the mounting of the PCB) wherethe array meets the block 110. Although more complicated (attaching thestrips 130, 131 is easy to do and the strips themselves are easy tomake), it would also be possible to omit a small region of theconductive layer 125 immediately adjacent to the metallic plates 120,121 and then to fill the gaps with some non-conductive material (whichmight even be a portion of the backing block 110 itself).

For well-known acoustic reasons, at least one matching layer is normallymounted on the upper, transmitting surface of the PZT element PZTelement 115. FIG. 1 shows two matching layers: a first, high-impedancematching layer 140, and a relatively lower-impedance matching layer 142,on which is mounted the lens 144.

The high-impedance matching layer 140 is preferably made of graphite,aluminum, or any other acoustically suitable material that is alsothermally conductive. This will then further heat transport to the sideplates 120, 121, especially if these extend along the edges of at leastthe high-impedance matching layer 140. The bottom surface of thehigh-impedance matching layer 140 is preferably provided, for example byplating (sputtering) or attached foil, with a layer 145 of anelectrically and thermally conductive material such as gold ornickel/copper. This layer 145 will not only conduct heat in theelevational direction away from the interior of the probe (the greatestarea of thermal build-up will typically be in the center of the lens144), towards the metallic plates 120, 121, but preferably also connectswith the electrical ground formed by the plates 120, 121. Note that thisreduces or eliminates the need for dedicated internal wires to provide aproper ground connection. Alternatively, if the high-impedance matchinglayer 140 itself is made of an electrically conductive material, then itcould eliminate the need for the conductive layer 145 altogether whilestill providing the desired thermal and electrical conductivity.

As FIG. 3 illustrates, the metallic plates 120, 121 could be allowed toextend along and be glued or otherwise attached to the outer edges ofone or both (or all) of the matching layers 140, 141. The outer edge(s)of the matching layer(s) may then be plated to provide better heattransport to and electrical contact with the plate(s) 120, 121.

In many prior art transducers, the PZT elements and matching layer(s)are mounted in a recess in the top of the backing block. This at leastpartially traps heat in the recess. In embodiments such as the onesillustrated in the figures, any or all of the matching layer(s) 140, 141may be made somewhat larger—as wide as or even wider than the topsurface of the backing block, with one or even both being in directthermal contact with the plates 120, 121. Together with the metallicplates 120, 121, this “oversized” matching layer structure may also addsome protection for the PZT array in case the probe is dropped orotherwise subjected to some kind of impact: Some of the impact forcewill be transferred to the plates, which can then also transfer some ofthe force to the backing block backing block 110 or to other probestructures such as its housing, depending on the chosen design of theprobe.

After the array 114 is laminated and diced (or the array is formed fromindividual PZT crystals), the plates 120, 121 are preferably added onthe side of the array. The top edge of each plate 120, 121 is thenpreferably glued or otherwise attached to the high-impedance matchinglayer 140 using, for example, electrically conductive epoxy glue.

In common prior art arrangements, a single-sided, double-sided, or evenmultilayered flex circuit (also known as a flexible printed circuit orFPC) with deposited traces is used to carry electrical signals from themain system, and between (not within) the backing block 110 and the PZTelement. In other words, the flex circuit is sandwiched between the PZTelements and the top of the backing block and extends laterally, in theelevation direction.

Such flex circuits, which are typically made of Kapton, along with theirdeposited traces, are usually more difficult to manufacture and are morefragile than standard PCB material. Moreover, being substantially rigid,a PCB is typically much more physically robust and does not require ascomplicated fabrication technology to work with successfully. Note thatthe preferred embodiment of one aspect of the invention does not needany flexible or otherwise non-rigid elements and provides one or evenmore thermal paths for heat to be removed from the PZT elements, thelens, etc. Furthermore, sandwiching a flex circuit between the backingblock and the array also means that it is generally more difficult toprovide a common electrical ground that is easily accessible by allinternal parts of the probe.

A PCB generally enables easier, more reliable, and more consistent probeassembly—in assembling known ultrasound probes that use flex circuits,at least one array element is often made useless because of the bendingof the flex circuit and breakage of the element's thin trace, andespecially where the flex circuit has electrically conductive vias toconnect traces. A suitable PCB may have traces up to about 20μ thick,that is, significantly thicker than what can usually be used reliably ona flex circuit, with no need for vias. A PCB is also usually muchcheaper (on the order of about 4%) than a flex circuit. Furthermore, forhigh frequencies, a sandwiched flex circuit can influence the acousticproperties and performance of an ultrasound probe.

One concern about mounting a PCB within the backing block 102 might bethat the backing block not be able to absorb all the generated sound itshould, but rather that some sound would travel into the PCB 102 itself,would reflect, and would cause image noise. Experiments have shown,however, that this concern is generally unfounded. In one prototype ofthe invention, for example, the PCB 102 was 0.4 mm thick and wasembedded in a backing block 11.6 mm thick. This provided attenuationgreat enough that no image was detectable on a standard oscilloscope;that is, the noise was at a negligible level. In general, the ratio ofthe PCB thickness to the block thickness should be low enough to avoidtoo much reflection. The proper thicknesses for any given application ofthe invention can be determined using known experimental design methods.

Nonetheless, as illustrated in FIG. 4, it would be possible to use aflexible material such as Kapton, that is, to use a flex circuit 402, inplace of the more rigid PCB 102 as long as its drawbacks are taken intoaccount and allowed for. (For clarity, in FIG. 4 the traces 104, 105 arenot included.) The thinner profile of the flex circuit may beadvantageous for some high-frequency probes, for example. One difficultyof this arrangement arises during the manufacturing process in thatthere typically must be some way to fix the flex circuit in the blockingframe as the blocking material is added and allowed to cure around theflex circuit. Any structure included within the backing block toaccomplish this, however, may then itself interfere with acousticintegrity by internally reflecting or conducting sound energy, whichcould cause image noise. Even if one were to use a flex circuit as inFIG. 4, however, the other advantages of the invention, such asefficient thermal conduction and electrical grounding would still beavailable, however.

Note that the structure shown in FIG. 4, in which the flex circuit 402is embedded within the backing block 110 and not just laid between theblock and the PZT array, is physically more robust than the prior artarrangement and eliminates the PCB-to-PZT interface that the prior artmust create during probe lamination. This not only reduces manufacturingcost, but also reduces the risk of breakage or faulty electricalcontact. The structure shown in FIG. 4 avoids still other known problemsof sandwiched structures such as the need for soldering to provide goodcontact between the flex circuit traces and the PZT elements. Becausethe flex circuit 402 in the illustrated embodiment does not enter fromthe side and does not lie between the backing block 110 and the PZTelement PZT element 115, it is relatively easy to add the metallicplates 120, 121, which can provide both grounding and heat sinking.

FIG. 5 illustrates another embodiment of a transducer according to thisinvention. In FIG. 5, the structures identical or at least equivalent tothose shown in FIG. 1 have the same reference numbers; the lens 144 hasbeen removed for the sake of clarity. In this embodiment, however,instead of separate metallic plates 120, 121, a single “box,” that is,enclosing member 520, which extends around the bottom and both sides ofthe backing block 110, but of course not obstructing the PZT elements inthe longitudinal direction forward. This box should also be made of athermally and electrically conductive metal such as aluminum, and couldbe fashioned by electroplating it onto the surfaces of the backing block110, or by forming aluminum foil or a sheet around the block and bondingit, or by any other known method.

As before, the PZT elements (of which one element 115 is shown) of thearray are mounted on the backing block 110, with the metallic layer 125in between forming a substantially full-surface contact electrode. Aswith the embodiment shown in FIG. 1, the PCB 102 is fixed within andextends longitudinally through the backing block. In the embodiment ofFIG. 5, the PZT element 115 does not extend laterally (in theelevational direction) all the way to the box 520. This is not required;rather, the width (as seen in FIG. 5) of the backing block relative tothe array width can be chosen using known design considerations. If thebacking block is wider than the PZT element 115, however, gaps 510, 512will be formed on either side of the PZT element and the box. These gapsmay be left unfilled; that is, they may be filled with air, which avoidscreating a heat trap, or they could be filled with an electricallynon-conductive but thermally well-conducting material to promote heattransfer to the box 520 without electrically shorting the PZT element115 with other elements.

In FIG. 5, the matching layers 140, 141 are included as before, as wellas the lens 144. In this embodiment, however, a layer 545—such as asheet of foil—of an electrically and thermally conductive metal likecopper is mounted between the innermost matching layer 140 and the uppersurface of the PZT element 115. This layer 545 extends out to and isbonded (for example by simple soldering) to the member 520. In FIG. 5,the layer 545 is bonded to the upper edges of the member 520, whichmakes for easy manufacture; the layer could also be attached to theinside surface of the member 520 adjacent to the upper edges, however,as long as care is taken to prevent any electrical contact between thelayer 545 and the layer 125. The layer 545 will then provide not only athermal path to the member 520, but will also provide good electricalgrounding to the common grounding structure that the member 520provides.

FIGS. 6A-6F illustrate the main steps involved in manufacturing theprobe shown in FIG. 1 and, with certain modifications that will beapparent to those skilled in the art, the other illustrated embodimentsof the invention as well.

FIG. 6A: Suitable PCB material is cut to size to form the PCB base 102.The traces 104 (and 105 on the back if needed) are then formed on thesurface(s) of the PCB 102 in the normal manner. If the PCB 102 is to bemulti-layer, then the traces will be formed using any known method.

FIG. 6B: The PCB 102 is put in a conventional backing blocker 600. Oneadvantage of using a PCB 102 is that it is relatively easy to fix itwithin the backing blocker, with no need for internal structures to keepit from flexing or warping or getting out of position, but that wouldremain within the cured backing block and potentially cause image noise.

FIG. 6C: The chosen material for the backing block 110 is added, withthe top edge of the PCB being flush with the top the backing block. Ifthe lead wires 106 (not shown) are needed at all and have not alreadybeen joined with the traces, then this can be done before or after thePCB 102 has been put in the backing blocker. (The PCB could be allowedto extend from the bottom of the backing blocker during addition of thebacking material.)

FIG. 6D: The conductive layer 125 is then sputtered or otherwise addedonto the top of the block, which will also cause the sputtering material(such as copper) onto the top edge of the PCB. Note that by the verynature of the sputtering process onto the edge of the PCB 102, some ofthe sputtered metal will also contact the top portions of the traces104, 105. In other words, as the inventor has confirmed throughfabrication experiments, the sputtering process will not only form thetop of the PZT electrode (the metallic layer 125), but will alsoestablish an electrical path from each trace to its respective portion(after dicing) of the layer 125.

FIG. 6E (see also FIG. 2): After preparation, for example, addition ofthe conductive layers 126 and 145, the PZT material (or individual PZTcrystals, if preferred) and matching layer(s) 140, 142 are then mountedon the backing block 110 using known methods. At this point, the arraywill essentially be a single large PZT element in contact with a singlelarge electrode (the metallic layer 125). The PZT material and matchinglayer(s) are therefore separated by dicing into the backing block 110 toseparate the PZT elements 115 both electrically and acoustically, suchthat one trace runs to a respective one of the PZT elements. Such dicingis common in transducer fabrication. Note that this dicing will alsoseparate the metallic layer 125 into “strips,” each corresponding to andin full bottom-surface contact with a respective one of the newlyseparated PZT elements 115. Heat will still flow outward (laterally,viewed as in FIG. 1) along each such strip, to the plates 120, 121. Theplates 120, 121 themselves, however, do not need to be physically cutinto pieces to prevent short-circuiting, since the easily installedinsulating strips 130, 131 will prevent this.

FIG. 6F: The insulating strips 130, 131 can then be attached along theintersection of the backing block 110 and the PZT array elements and themetallic plates 120, 121 can be mounted onto the backing block backingblock 110. Alternatively, the enclosing member 520 can be electroplatedor other formed on the backing block 110. The kerfs left from dicing canalso be filled with any conventional material 214, which can be done atthe same time the lens 144 is attached and may in fact be the same asthe material that forms the lens.

1. An ultrasound imaging transducer comprising: an array ofelectro-acoustic elements; a backing block with a planar, non-recesseddistal surface on which the array is mounted; for each electro-acousticelement, an area of electrically conductive material on a correspondingportion of a contact surface of the backing block and in electricalcontact with the electro-acoustic element; a substantially rigid printedcircuit board (PCB) secured to the backing block and extending in alongitudinal direction substantially perpendicular to the contactsurface; and for each electro-acoustic element, at least oneelectrically conductive trace on the circuit board and in electricalcontact with the corresponding contact surface portion and thereby withthe electro-acoustic element, a solder-free electrical signal paththereby being formed through the trace to the electro-acoustic element.2. The transducer of claim 1, in which the circuit board is embeddedwithin the backing block.
 3. The transducer of claim 1, in which theelectrically conductive material is sputtered onto the contact surfaceof the backing block.
 4. The transducer of claim 1, in which the PCB ismounted on a lateral surface of the backing block.
 5. The transducer ofclaim 1, further comprising at least one metallic member located on atleast one side surface of the backing block, extending longitudinally atleast as far as the array, and forming a common electrical groundcontact.
 6. The transducer of claim 5, further comprising anelectrically insulating element separating the metallic member from theelectrically conductive material on the contact surface of the backingblock.
 7. The transducer of claim 5, in which the metallic memberincludes at least two metallic portions mounted on opposing sidesurfaces of the backing block, both plates being substantiallyperpendicular to the contact surface.
 8. The transducer of claim 7, inwhich each metallic portion is in physical contact with lateral surfacesof the electro-acoustic elements.
 9. The transducer of claim 5, furthercomprising at least one acoustic matching layer mounted on atransmitting surface of the electro-acoustic element.
 10. The transducerof claim 9, in which an edge region of each metallic portion of eachmetallic member is in thermal contact with a respective edge portion ofthe matching layer.
 11. The transducer of claim 10, further comprising athermally conductive, metallic layer between the matching layer theelectro-acoustic element and in contact with the metallic member. 12.The transducer of claim 1, in which the electro-acoustic element is madeof lead zirconate titanate (PZT).
 13. The transducer of claim 1, furthercomprising an acoustic lens mounted longitudinally outward on thematching layer(s).
 14. A method for manufacturing an ultrasound imagingtransducer assembly comprising: applying electrically conductive tracesto at least one surface of a rigid printed circuit board (PCB); forminga backing block with the PCB secured to the backing block; sputtering anelectrically conductive layer onto a distal, non-recessed, planarcontact surface of the backing block and a top edge of the PCB; mountingan electro-acoustic material on the contact surface of the backingblock; mounting at least one matching layer on the electro-acousticmaterial; dicing the matching layer, the electro-acoustic material, andthe electrically conductive layer into an array of electricallyseparated portions, each portion of the electro-acoustic materialthereby forming a separate electro-acoustic element and each portion ofthe electrically conductive layer thereby forming an electrodeconnecting the electro-acoustic element to at least one of the traces;on at least one side of the backing block, mounting a metallic member incontact with a lateral edge of the backing block and electricallyinsulated from the electrically conductive layer portion.
 15. The methodof claim 14, further comprising embedding the PCB in the backing blockduring the forming of the backing block.
 16. The method of claim 14,further comprising mounting each metallic member so as to be inelectrical contact with the matching layer.
 17. The method of claim 16,further comprising applying a conductive material to the matching layerand mounting each metallic member so as to be in electrical contact withthe conductive material of the matching layer.
 18. The method of claim14, further comprising mounting an acoustic lens on the matchinglayer(s).
 19. A ultrasound imaging transducer comprising: an array ofelectro-acoustic elements; a backing block on which the array ismounted; for each electro-acoustic element, an area of electricallyconductive material on a corresponding portion of a contact surface ofthe backing block and in electrical contact with the electro-acousticelement; a circuit substrate secured to the backing block and extendingin a longitudinal direction substantially perpendicular to the contactsurface; and for each electro-acoustic element, at least oneelectrically conductive trace on the circuit board and in electricalcontact with the corresponding contact surface portion and thereby withthe electro-acoustic element; at least one acoustic matching layermounted on a transmitting surface of the electro-acoustic element; atleast one metallic member mounted on a lateral surface of the backingblock and extending in a longitudinal direction at least as far distallyas a distal surface of the electro-acoustic elements; and a thermallyconductive, metallic layer located between the at least one acousticmatching layer the electro-acoustic element and in contact with themetallic member; said at least one metallic member thereby forming aheat sink for heat flowing through the thermally conductive, metalliclayer, as well as laterally from the electro-acoustic elements.
 20. Theassembly of claim 19, in which: the backing block has a planar,non-recessed distal surface on which the array is mounted; the array ismounted on the distal surface of the backing block; the circuitsubstrate is a substantially rigid printed circuit board (PCB) embeddedwithin the backing block and extending in a longitudinal directionsubstantially perpendicular to the contact surface.
 21. The assembly ofclaim 19, in which the electrically conductive material is sputteredonto the contact surface of the backing block.
 22. The assembly of claim19, in which each metallic member is located on a respective sidesurface of the backing block, extends substantially perpendicular to thecontact surface and distally at least as far as the array, and forms acommon electrical ground contact for the electro-acoustic elements. 24.The assembly of claim 22, in which each metallic member is in physicaland thereby thermal contact with lateral surfaces of theelectro-acoustic elements.
 25. The assembly of claim 22, furthercomprising lateral gaps on either side of each electro-acoustic elementbetween the electro-acoustic element and the metallic member, theelement thereby being physically separated from the metallic member butthe metallic member still receiving heat from the element.
 26. Theassembly of claim 22, in which the metallic member is formed of twolaterally opposing plate-like elements.
 27. The assembly of claim 22, inwhich the metallic members are portions of a single metallic pieceextending on either side of and across a proximal surface of the backingblock.
 28. The assembly of claim 19, in which the electro-acousticelement is made of lead zirconate titanate (PZT).
 29. The assembly ofclaim 19, further comprising an acoustic lens mounted longitudinallyoutward on the matching layer(s).
 30. The assembly of claim 19, in whichthe metallic layer is metallic foil.
 31. A ultrasound imaging transducercomprising: an array of electro-acoustic elements; a backing block witha planar, non-recessed distal surface on which the array is mounted; foreach electro-acoustic element, an area of electrically conductivematerial on a corresponding portion of a contact surface of the backingblock and in electrical contact with the electro-acoustic element; asubstantially rigid printed circuit board (PCB) embedded within thebacking block and extending in a longitudinal direction substantiallyperpendicular to the contact surface; and for each electro-acousticelement, at least one electrically conductive trace on the circuit boardand in electrical contact with the corresponding contact surface portionand thereby with the electro-acoustic element, a solder-free electricalsignal path thereby being formed through the trace to theelectro-acoustic element; metallic members mounted on opposing lateralsurfaces of the backing block, each extending in a longitudinaldirection at least as far distally as a distal surface of theelectro-acoustic elements and forming a common electrical groundcontact; at least one acoustic matching layer mounted on a transmittingsurface of the electro-acoustic element; an acoustic lens mountedlongitudinally outward on the matching layer(s); and a thermallyconductive, metallic layer located between the at least one acousticmatching layer the electro-acoustic element and in contact with themetallic member; said at least one metallic member thereby forming aheat sink for heat flowing through the thermally conductive, metalliclayer, as well as laterally from the electro-acoustic elements.
 32. Theassembly of claim 32, in which the metallic members are portions of asingle metallic piece extending on either side of and across a proximalsurface of the backing block.